Automatic apparatus for administering drugs



Sept. 28, 1954 R. G. BxcKFoRD AUTOMATIC APPARATUS FOR ADMINISTERING DRUGS 6 Sheets-Sheet l Filed NOV. 13, 1950 Q .aux

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AUTOMATIC APPARATUS FOR ADMINISTERING DRUGS Filed Nov. l5, 1950 6 Sheets-Sheet 5 Sept 28, 1954 R. G. BICKFORD 2,690,178

AUTOMATICy APPARATUS FOR ADMINISTERING DRUGS Filed Nov. 13, 1950 6 Sheets-Sheet 4 0 /O/ l 5 9503 /04 z Flc. IO

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Sept. 28, 1954 R. G. BlcKr-'ORD AUTOMATIC APPARATUS FOR ADMINISTERING DRUGS 6 Sheets-Sheet 5 Filed NOV. 13, 1950 Sept. 28, 1954 R. G. BICKFORD AUTOMATIC APPARATUS FOR ADMINISTERING DRUGS Filed Nov. 13, 195o 6 Sheets-Sheet 6 I N V EN TOR. #PEG/NAL@ GY Bmx/#ORD "6M, www@ A fro/QN: :fs

Patented Sept. 28, 1954 UNITED STATE-LS FENCE AUTOMATIC APPARATUS FOR ADMINISTER- ING DRUGS Application November 13, 1950, Serial No. 195,343

(Cl. 12S-213) 16 claims. 1

This invention relates to automatic apparatus for the administration of drugs generally, and more particularly anesthetics to a patient in response to an electrical signal originating in the patient or generated as a result of a bodily function of the patient. There are many drugs, the administration of which should be in accordance with the response of the patient. Heretofore, administration oi such drugs has been based solely upon the general experience of the physician With the use of the drugs, plus such outwardly visible, audible or otherwise sensible symptoms of response as may be observed by the physician during administration of the drug.

I have discovered that the use of anesthetics such as ether or barbiturates (for producing anesthesia) or the use of anticonvulsants, such as pentothal, luminal or amytal for treatment of the condition of continuous epileptic seizure and in the use of many other drugs the patients respense may be utilized for controlling the rate of drug administration. rEhe response of the patient is either the electrical Wave pattern of the patient (su-ch as the electrical brain wave pattern) or an electrical signal generated in consonance with a L his sense organs (eyes, ears and hands) which he evaluates and, in the light of previous experience, utilizes to form an estimate of the patients depth of anesthesia. He compares this estimate nientally with a standard depth of anesthesia, 1cased upon his previous experience, and on the basis of that experience administers the anesthetic to the patient in an amount such as is required by the surgeon for a particular stage of the operation, and then takes appropriate action to increase or decrease the anesthetic concentration as the operation progresses, or in accordance with the surgeons request. The administration of anesthesia in accordance with this known manner is subject to several faults. As a rst form of error, the anesthetist may not properly evaluate the information received from the patient, with a consequent erroneous estimate of the anesthetic depth. Thus, an inexperienced or inattentive anesthetist may not properly evaluate the appearance of the eyes, the sound of the patients breathing, or the rapidity and strength of the patients pulse, and consequently malte an erroneous or mistaken estimate of the depth of anesthesia with the result that the anesthetist may erroneously administer or fail to administer requisite anesthetic.

A second form of error may be characterized as the slowness or lag in the response of the anesthetist to information received from the patient, with the result that the anesthetic is administered too late, in respect to the depth of anesthesia at any particular instant. As a consequence even among experienced anesthetists the patient is not infrequently alternately overanesthetized or under-anesthetized, sometimes with wide variations between these extremes.

Studies made in this invention have shown that in the animals investigated, namely rabbit, cat, monkey and man, a simple and characteristic relationship exists .between the depth of anesthesia produced by anesthetics such as the barbiturates or ether and the integrated potential output of the cortex of the patient. Thus, in accordance with this invention it has been discovered 'that electrical integration of the amplified electroencephalographic signal may be utilized as the basis :"or administration of the anesthetic. )It has further been discovered that administration of the anesthetic may be accomplished automatically in relation to the integrated, amplied electroencephalogram, and that varying depths of anssthesia may be selected as desired. lt has also been discovered that hy limiting response to certain electrical frequencies produced by the brain wave for utilisation in the automatic administration of anesthesia, it is possible to avoid interference dus to low and high frequency extraneous signals.

lt has also been. discovered in accordance with the invention that the amplied brain potential may be compared with a standard voltage and the diierence 'therefrom utilized for actuating the administration of anesthesia, thereby to provide an error-actuated system.

lt is a general object of the invention to provide a method and apparatus for administering drugs to a patient in response to a signal produced by or in consonance with a function or functions of the patient.

It is a further general object of the invention to provide methods and apparatus for administering drugs, such as anesthetics, anti-convulsants or the like to a patient in response to a signal function of the patient or in response to an electrical brain wave function cf the patient.

It is a more specific object of the present invention to provide an apparatus and method for administering anesthesia which is automatic in character and in which the anesthesia is administered responsive to the potential output of the cortex of the patient.

Itis a further object of the invention to provide `.whereinelectrical signals from the scalp of the l `patient are amplified, rectified and stored as a `charge on an electrical condenser, and wherein l the charge is from` time to time utilized for proportionately delivering anesthetic to the patient. f- Itlis `an additional object of the invention to record of anesthetic administration being shown for each condition;

Figure 2 corresponds to Figure 1 except where the anesthesia is ether. This figure likewise shows the brain wave potentials when the patient is resting and during light anesthesia, moderate anesthesia and deep anesthesia, the related record of anesthetic administration being shown for each condition;

Figure 3 is a schematic view showing the wiring diagram of the apparatus of the invention, together with the mechanical components shown attached to -the patient; 1w 'w Figure 4 is a plan View of the stepping relay and associated apparatus used for administering the anesthesia to the patient;

Figure 5 is a side elevational view in the direction of arrows 5-5 of Figure 4, showing the stepping relay and mechanical apparatus associated therewith for moving the anesthetic to the patient;

Figure 7 is a sectional view taken along the line 1 1 of Figure 4, partly in section, showing the steppingrelay in another position as compared .with Figure 4;.. .f

Figure 8 is a sectional view taken along the line and in the direction of arrows 8 8 of Figure 4 and shows the screw block which is actuanesthesia administering syringe; i

provide an apparatus wherein amplified, rectified and integrated electrical signals received from the scalpfof the patient are usedtocharge a condenser to a specified voltage and wherein an auxiliary circuit lis utilized automatically to discharge i said condenser when the voltage reaches a prescribed amount, and upon discharge Vof the condenser to use a signal thereby established for motivating a pump for `moving `anesthetic from a supply to the patient andr for u,making a record of such delivery.

. v,It is another object of the invention to provide a method and apparatus wherein anesthetic lis administered at a rate proportional to the variation of the brain potential signal from an established potential so as to provide an error-actuated system.

It is a further object of the invention to provide` av method and apparatus wherein the sigthe patient. i i

Other and further objects of the invention are `those inherent in the apparatus herein illustrated, described and claimed.

i The invention is illustrated with reference to Athe `drawings in which corresponding numerals refer to the same parts and in which Figure 1 is a diagram showing the brain wavepotentials and related `signals showing administration of anesthesia where the anesthesia is pentothal, for conditions in which the patient is resting,

for light anesthesia, moderate anesthesia and deep anesthesia, the related ure 3, modied to include the band pass filter;

Figure 9. corresponds to Figure 8 and shows the screw blockin open position for purposes of adjustment;

. Figure 10 is a side elevational view of an electrical pump utilized insome instances for pumping an anesthetic such as ether;

Figure 1l is a schematic view similar to Figand Figure 12 is a schematic view likewise corresponding to Figure 3 showing an error-actuated system. l

The methods and apparatus of the invention relate broadly to automatic administration of drugs `to a patient in response to a signal function orginating in or generated in consonance with a physical function of the patient. Such signal functions generated in the patient are broadly denoted the physiological electrical potentials of the patient, and that term will be `used in the present specification and claims broadly to denote such signal functions. The most common situation in which the invention is of particular usefulness is the automatic administration of anesthetics, which the instant discoveries and/or invention for the iirst time makes possible. `There are many other uses,

. however, such as the automatic administration `of anti-convulsant drugs in the treatment of conto control the rate at which the drugs, etc. are

administered to the patient. Therefore, the invention described and claimed must be considered broad.

However, for simplicity in explanation but without limitation of the scope of the invention and/or discoveries described and claimed, this specication will particularly refer to that instance in which this subject has most widespread usefulness, namely for the administration of anesthetics. Therefore, it will be understood that while the illustrations are specific, they do not limit the scope of the invention.

The electrical brain wave signal function has a variety of names. Thus, it is sometimes called the "electroencephalographic potential. In the Mayo Clinic wherein there was done the work upon which the present invention is based, this electrical brain wave signal is often called the EL E. G. which is an abbreviation for electroencephalogram. Again, such brain wave signal has been called Cortical potential. For the purposes of this specification and claims the term electroencephalographic potential will be used to denote such Ibrain wave signal function.

Method phases of the invention can be explained most easily with reference to the drawings related to the invention. Thus, referring to the drawings and particularly to Figures 1 and 2, in each of these figures there are illustrated related resting light anesthesia, moderate anesthesia and deep anesthesia conditions of oscillographic records. These oscillographic recordings are, in each instance the electroencephalogram recording of the brain potential or "electroencephalographic potential of the patient. With each such recording there is shown the related record of administration of anesthetic which is carried out in accordance with the method of the invention. Figure 1 shows these factorss Where the anesthetic is pentothal, .which is injected into the patients vein by means of a suitable syringe. In Figure 2 the aforesaid factors are shown where the anesthetic is ether, which is administered to the patient by utilizing the pumping apparatus or syringe of the invention, to supply the ether to the air system of the patient, as fby the use of a customary respiratory vaporizer and mask, into which the anesthetic is pumped or injected in accordance with the actuation of the apparatus of the invention.

Referring to Figure 1 it has been discovered in accordance with the invention that the brain wave pattern or electroencephalographic potene tial under the condition of resting (which is shown opposite the bracket marked Resting) is a complex pattern composed of varied frequencies, the signals being of considerably variable amplitude. As the condition of the patient reaches what is known as light anesthesia (the record of which is shown opposite the bracket so marked), the brain wave pattern increases in amplitude and the lower frequencies seem to predominate or at least to overshadow the higher frequencies insofar as amplitude is concerned, as compared with the resting condition. As the condition of the patient reaches what is known as moderate anesthesia the brain wave signals or electroencephalographic potential of the patient includes pulses of signals at spaced intervals, yet the amplitude of the individua-l pulses Iproduced is of about the same order and magnitude as those in the resting and light anesthesia conditions. In this moderate stage of anesthesia there are medium to long intervals during which the signal is of only small amplitude at relatively higher frequency. When the patient reaches a condition of deep anesthesia, the brain wave pattern of electroencephalographic potential shows only a very small amplitude higher frequency voltage variationfor long intervals and with only an occasional lower frequency, larger amplitude wave imposed thereon at relatively infrequent intervals. The brain wave frequencies are mostly within the range of 3 to 30 cycles per second and the lower and higher frequencies referred to in this ex planation are within substantially that range.

The brain wave patterns or electroencephalographic potentials produced when the anesthetic is ether are of generally the same pattern. Thus, during the "resting period the high and low frequencies (mostly within the range of 3 to 30 cycles per second) are inter- IniXed and a complicated wave pattern results, the average amplitude of which is comparatively much less than during conditions of light anesthesia where the lower frequencies in said range seem to increase in amplitude and predominate. Again, during conditions of moderate ether anesthesia, there are increasing intervals of very minor brain wave signals interspersed with groups of mixed frequency signals having an amplitude of the same order and magnitude as that of light anesthesia, but the duration of the signals forming the groups is of much less while under conditions of deep ether anesthesia the lbrain wave signal constituting the electroencephalographic potential settles down to a very minor signal with moderate amplitude pulses only at very infrequent in tervals.

From the brain potential curves for the resting, light anesthetic, moderate anesthetic and deep anesthetic conditions, shown in Figure 1 and 2, it will be observed that regardless of whether the anesthetic is pentcthal or ether, the brain (cortex) potential or electroencephalographic potentials, if considered as energy, increases from the condition of resting to the condition cf light anesthesia and then decreases through the moderate anesthesia to a minimum at the deep anesthesia condition. Conversely considered, the energy of the brain (cortex) wave increases from the condition of deep anesthesia and continues to increase through the condition of moderate anesthesia to the condition of light anesthesia. Advantage is taken of this discovery so as to provide for the administration of additional anesthetic when the patient begins to recover from a condition of deep or moderate anesthesia and such administration of anesthetic again brings the patient back to the level of anesthesia, depending upon the adjustment of the system.

in Figures 1 and 2 there are shown records of anesthetic administration above each brain wave pattern. These records or traces are horizontal lines with an occasional short verticai line or pip thereon which indicates the administration to the patient of measured dose (unit amount) of anesthetic for the particular condition being recorded. Thus, for the resting condition, Figure 1, the record of pent-@thai administration (which is the horizontal line with 5 (rive) pipe on it above the chart showing the electroencep-halographic potentials shows such (five) units or pips for the time period covered by the record, whereas during iight anesthesia there were 1l (eleven) units of pentothal administered which is due, as will later be shown, to the greater integrated amplified brain wave signal. To continue, when the patient reached the condition of moderate anesthesia there were again 5 (five) units of anesthetic (pentothal) administeredgenerally in ktime with the lower frequency pulses ofthe patients brain wave pattern, and when the condition of deep anesthesia was reached only f1, (one) unit of anesthetic was administered 'as indicated by the one fpip on the trace.

yReferring to Figures 3-9 the apparatus of the invention therein shown is one exemplary form of system for carrying out the method phases of the invention. Other forms are illustrated in Figures `11 and 12.

Referringto Figure 3 the system generally includes a responsive-connection to the patient and `an amplifier generally designated I6. The output of amplifier I6 shown under the bracket I is coninected to the input of the anesthesia administering circuitshown opposite the bracket II and is optionallyalso connected to one element of a ytwo-element recording oscillograph shown under bracket III. The electrical circuits for control- 4ling the administration of the anesthesia shown opposite the bracket II have their output connected to the anesthesia administering device shown under the bracket IV, and such output circuits may also be connected to the second 'element of the two-element recording oscillograph III. The anesthetic administering device isconnect'ed back to the patient.

Thus, as shown in Figure 3 a connection is made by means of a small barbless hook IIJ to one part of the scalp of patient P and another connection is made by means of a similar small barbless hook to another portion of the pa- `results, they are preferably made to the forelpart and rear part of the scalp, as illustrated.

Itis only necessary that these hooks be inserted lightly under the skin in order to be responsive `to the brain wave pattern of the patient P.

The 'amplifier I6 is a push-pull amplier of vconventional construction having input terminals connected to hooks I and and input ground I3 connected to hook I2. The amplifier has output terminals 1, I8 and I9. The signal is derived between the output terminals Il and I8, of which the latter is grounded, the signal von circuit I9 being wasted, so far as the system is concerned. The terminal is connected through line to junction 2| and thence continues through line 22 to condenser CI and thence through line 23 to one terminal of the resistor RI and through that resistor to junction 24 on line L2. Terminal |8 of the amplifier is connected through line 25 to junction 26 and thence through line 21 to junction 28 on line L2.

The amplified brain potential signal, which may also be designated the amplified potential of the cortex or amplified electroencephalographic signal is thereby impressed through condenser CI upon the resistor RI.

The anesthesia administering circuits shown opposite the bracket II have power input lines LI and L2 upon which a unidirectional potential of approximately 260 volts (for the specific circuits illustrated) is applied. Line LI extends through junction and thence through resistor R|4 to junction 3|, on line LIa, which extends through junctions 32, 33, 34 and 35 `to one terminal of the voltage regulator tube V2 to ljunction 36 on line Llb, and thencethrough line Llb to a terminal of a second voltage regulator tube VI which has its second terminal connected through line 31 to junction 28 on line L2. The tubes VI and V2 are conventional voltage regulator tubes. The tube VI has a potential `drop of volts across it and tube V2 has a potential drop of 108 volts across its terminals. Tubes VI and V2 accordingly establish a potential of 150 volts on line Llb relative to line L2 yanda potential of 258 volts on line Lla, relative to line L2, these potentials being regulated by the action of tubes Vl and V2, regardless of `momentary voltage uctuation on the supply lline LI. If a separate circuit of regulated voltage'is available, the tubes VI and V2 may be dispensed with, or in those instances where supply voltage is sufiiciently free from variation, `the voltage regulation tubes may likewise be dispensed with. The particular potentials given for tubes VI and V2, and the other specific constants mentioned herein for the remaining components of the circuit are merely illustrative. It is, of course, obvious that the circuit can be designed with equal facility for other potentials and using other constants.

Tube V3 is of the five element type and has a heated cathode 40, a control grid 4|, a first screen grid 42 and a second screen grid "43, together with the anode 44, and'serves to amplify and rectify the amplified brain potential signal (or cortex potential or electroencephalogram, however designated). The cathode 40 is heated by a filament not illustrated and is connected through junction 45 and through junction 46 `to resistor R3 which is in turn connected to junction 48 on line L2. Thecontrol grid 4| is connected through line 49 to the adjustable terminal 50 on resistor Rl, which may be moved along the resistor RI to vary the input and hence the level of response of the system. Resistor RI controls the depth of anesthesia of the patient "in the overall operation of the system.

Grid 42 is connected through the variable tap 5| on resistor R2 which is connected by a line 52 to junction 4l on line L2 and has its opposite end connected through junction 53 to junction 36 on line L|b. The adjustment of tap 5| accordingly `controls the potential applied to the rst screen grid 42 and hence the level Aof activity of tube V3. The second screen gridv43 is connected to the cathode circuit at junction 45. A circuit extends from junction 53above Iresistor R2 thence through line 54 and through resistor R4 to junction 46 on the cathode terminal of tube V3. From the anode 44 a circuit extends through the milliammeter 55 to` the junction 56 and thence through condenser C2 to the junction 35 on the voltage regulated line Llw.

The capacitor C2 is a storage capacitor which accumulates and hence integrates the amplified brain wave signal. In the operation of the system the capacitor C2 is discharged whenever its voltage level reaches a prescribed value and in practice the periodicity of discharge is proportional over a measured longer time interval, to the integral of the amplified electroencephalographic potential (cortex potential). Condenser C2 serves as means for accumulating an electrical charge at a rate proportional to the integration of the electroencephalographic potential signal of the patient.

The discharge of capacitor C2 whereby the stored electrical energy is dissipated from time to time is accomplished by a triggering circuit composed of a pair of thermionic tubes V4a and V41) and associated circuit components which are connected in what is known as a flip-nop circuit. Such a two-valve flip-nop triggering circuit is described in detail in the work of Puckle entitled Time Basis, page 50 et seq., published 1943 by John Wiley & Sons, Inc. In detail, the connections to the flip-flop triggering circuit include line 60 extending from junction 56 below capacitor C2 to the cathode 5| of tube Vila, the anode 62 of that tube being connected through junction 63 and thence through resistor R5 to junction 33 on line Lla. From junction 32 on line Lia a circuit extends through resistor R7 and through junction 64 to the anode 55 of the tube V4b, the cathode 56 of said tube being connected through line to the junction 68 on line L2. A circuit extends from junction 69 on line L2, thence through resistor R5 to junction 79, which is connected to the grid of the tube Vlb, and is also connected through the condenser C4 to junction 53 on the anode lead of the tube Vila. The control grid l2 of the tube Va is connected through line i3 to junction 64 on the anode lead of tube V412.

From junction 34 on line LIa a circuit extends through line l5, through condenser C3 to the junction 15 on line L2.

The junction 64 forms the signal output terminal of the flip-dop circuit composed of tubes Vila and V473 interconnected as described. From junction 64 a circuit extends over line 'i4 through condenser O5 and thence to junction 'il and line |23, thence through resistor R8 to junction 19 on line L2. The tube V5 is of the thyratron type and has a cathode 80 that is connected through junctions 8| and 82 and thence through resistor RH) to the junction 83 on line L2. The control grid 94 of the tube V5 is connected through resistor R9 to junction 'il on the signal input circuit, the screen grid 85 of the same tube being connected by line t to junction 8| on the cathode circuit. The anode 88 of tube V is connected through junction 89 and resistor RIZ, junction 90, thence through resistor RIS to junction 30 on line Ll. tube V5 is between terminals 82 on its cathode lead and S9 on its anode lead. The terminal 82 is connected by line 9|, through junction 92 to one terminal of the coil 93 of a stepping relay generally designated |00. From junction 89 on the anode lead of tube V5 the circuit extends through condenser C6, thence via line 94 and through junction 95 to the otherl terminal of thecoil 93 of the stepping relay |00. A circuit also extends from junction 90 (between resistors R|2 and RlB) thence through condenser C1 and through line 96 to the terminal 91 on line L2, and a circuit extends from junction 82 (on the cathode lead of tube V5) through resistor Ril to junction 3| on line Lla.

The stepping relay which serves as a motor for driving the transfer means by which the anesthetic or other material is administered to the patient is best illustrated in the enlarged views of Figures 4 through 9. The relay or motor has a frame |00 which serves to supportthe magnet coil 93, the frame |00 being provided at one end with upstanding side pieces |0| and |02 which at their upper ends serve to support the pivot shaft |03 to which an armature |04 is The output of r connected. The shaft |93 has a crank arm |05 rmly attached thereon which extends outwardly, and to the outer end of it there is attached one end of a spring |96, the other end of the spring being anchored on the side arm lill of the frame piece itl. The spring |00 tends to move the crank |015 in the direction of arrow |09, consequently turning the shaft |93 in the direction of arrow |02 and thus moving the armature |04 away from the pole piece |||l of the magnet. From the shaft |93 there also extends a long side arm which reaches out beyond the coil of the magnet and at its outer end is provided with a spring dog 2 having an inwardly bent lower end H3 which is adapted to engage the teeth in the ratchet wheel ||4. An eccentric boss is provided at ||5 which may be adjusted to engage the back side of the lower end l i3 of the dog and hence insures its engagement with the ratchet wheel H4. The arm is moved up and down in the direction of the arrow ||6 (Figure c) and ||7 (Figure 7). The arm is pulled downwardly by the action of spring |96 when the magnet coil 93 is de-energized, but when the coil is energized the attraction of 'the armature |04 to the pole piece ||0 causes the arm to be moved in the direction of arrow to the position shown in Figure 7, against the action of spring |05. This up and down swinging movement of the arm which occurs each time coil 93 is energized serves to move the ratchet wheel ||9 around, one tooth for each energization of the coil 93. The frame |00 of the relay also has a spring dog at l it which prevents backward rotation of the ratchet H4. The net result is to produce rotation of the ratchet wheel I4, one tooth at a time, and this step-by-step rotation is utilized for the rotation of a screw |20.

The frame of the relay is provided with a flange |2| at one side which serves to support a pair of guide rods |22 which have their outer ends connected by the bearing plate |23, the outer end of the screw |20 being journalled at |24 in that bearing plate. The parallel guide rods |22 serve as a cross-head on which there is slidably mounted the block member generally designated |25 which is best shown in Figures 8 and 9.

The block member |25 is composed of two halves |25A and |25B which are arranged so that they can be pushed apart so that the block can be disengaged from the screw |29 to allow it to be moved along the rods |22 and screw |20 for rapid adjustment of the position of the block |25 along the length of the screw. The two halves |25A and |25B of the block |25 are held 'together by a pair of pins |20|26 which are threaded into the block |2513 so as to be movable therewith. The pins |25 pass through the holes |2`-|2l of the block |25A. rThe outer ends of the pins |29 are fastened together by a bar |28 and between the bar and the slider half 25A there are springs |29-l29 which surround each of the pins |26. As a result of the action of the springs |29, the half |25A of the slider is forced towards the half |2513, thus causing the slider neatly to close into the unitary whole as shown in Figure 8. The two halves |25A and |25B, considered as a unit, are provided with a pair of holes |32-i32, one half of the hole being in each half of the slider. These holes are arranged so as to nt on the parallel rods |22 and have an internal diameter such that when the slider is l l in the closed position shown in Figure 3, it will slide easily yet without sloppiness upon the rods 122. The slider is also provided with a central aperture at 133 which is threaded to correspond with the threads on the rod H20. Therefore, when the slider is in the condition shown in Figure 8 and the threaded rod 120 is revolved by the action of the ratchet wheel 114, the slider is caused to progress in the direction of the arrow |35. For each stepping action of the relay the slider moves one slight increment longitudinally in the direction of arrow 135. The slider or block 125 has attached to it a stirrup at 136 which reaches out beyond the end frame 123 even when the slider is retracted to a position against the frame member 121. This stirrup is a simple bent piece of metal having an end portion |31 which abuts against the movable piston (plunger) 140 of the syringe generally designated 141, which serves as an anesthetic supply reservoir, the inge being mounted nxedly by means of a bracket or clamp |42. The frame of the stepping relay 100 is, of course, also xedly mounted and therefore when the relay is actuated stepb'y-step the slider |215 moves step-by-step in the direction of arrow 135 and the end |31 of the stirrup 136 pushes against the plunger 140 of the syringe and for each step of movement of the relay the syringe is thus likewise moved one step, thereby causing the anesthetic which is contained iny the syringe tobe ejected from the hypodermic needle 143. The hypodermic needle 143 is suitably connected to the patient in accordance with approved medical procedure. Where the anesthetic is ether the hypodermic syringe may be likewise filled with ether and connected by a tube to the sponge in the respiratory mask of the patient, or to any other ether administering instrumentality in the air system of the patient. The stepping relay and the syringe thusr serve as a material supply and material' pump means by which the required material is fed to the patient.

Where ether is used as the anesthetic the entire stepping relay |60 may be substituted with the pumping system shown in Figure 10, which serves as the transfer means by which the anesthetic is fed to the patient. In this figure the pump generally designated 150 is an impulse operated pump of the type commonly used for pumping gasoline for automotive engines. Such pumps operate one stroke for each electrical energization or pulse applied to the wires 151 serving the electrical coil of the pump. The pump, per se, forms no part of this invention and is merely utilized for pumping ether from the supply can or reservoir 153 out through the outlet pipe |52 of the pump which is connected to the respiratory mask or other instrumentality used for administering the ether to the patient.

In thisrorm the can or reservoir i525 and pump |50 are the material supply means and material pump means.

Referring again to Figure 3 where the system is used for research work it is especially desirable to maintain a record of the brain Wave pattern (or potential output of the cortex or electroencephalogram, however designated) of the patient as compared to the operation of the instrument, In order to make such records a twoelement recording oscillograph may most conven-iently be used. This oscillograph is illustrated under the bracket III of Figure 3 and has a pair of terminals 154 and 155 which are connected through the manual switch 156 and thence through lines |51 and4 1585to the terminals 21 and 26 of the amplil'ler` 1'6. Thus, the' brain wave pattern may be recordedy byone element of the recording oscillograph. They other element of the recording oscillograph isl connected from a pair of terminals I'59` and 166",- through lines 1.61 and 162 and thenceZ through the manual switch 163 to the terminals 9B and' B2, respectively, on the `circuit which is connected either to the'lstepping relay device 160 shown in Figure 1 orl to the ether-pump shown? in Figure 10, it beingunderstood that the'fether pump terminals 15| may be connected in place of the' coil 93 of the stepping relay, vdepending upon the type ofanesthetic administeringdevice desired. Accordingly, with the recording device, as illustrated, the attendant physicians have a complete record of the bx'ainwave` pattern of the patient and a simultaneous and related record of theoperation of thev anestheticadministering system. Such records are illustrated` in Figures 1 and 2.

Operation-It willlbe assumed' that the' Voltageregulating tubes V1 and V2. are utilized and they accordingly establish regulated voltages' as previously described on lines Lla and Lllb; It is'. also assumed that the condenser which is the storage condenser', has' just been discharged, thus disspating any charge previously upon it. Accordingly,A the potentalat terminal 56 (below condenser CIT) is at approximately the voltage of line Lla. Under such conditions tube Vdb is conductive and current vflows 4from' line1L|a through resistor R1 and from the anode 65 tothe cathode 66 of thetube V417 through line 6l' of line L2. The size -of resistor R1 .ismade such that With'current owing through tube Vith (and with the supply voltages and constants above mentioned) a voltage of approximately 80-1'00 volts is maintainedvat junctiol'lG.` This is less than the voltage at 56.

The brain wave signal derived from the' patient (or a potentialoutput ofth'e cortexr or electroencephalograpliick potential, as variously designated) after amplification by means of the amplifier I6 is applied through lines 22. and 21 and condenser C1 across the resistor R1', This brain wave signal, as amplifiedpis affaithful reproduction of the originalfbrain wave signal except that it is on an amplified scale. A selected portion of this signal is picked off' by meansot the adjustable tap 56 on the-resistor' R1 'and is applied. to the control grid 411l of theamplifierrectier V3. The outputfof tube V3 is the rectified and amplified half` wave corresponding to one half of thev amplified-inputsignat Gor' that portion of it selected onthev adjustable resistor R1) and such output of tube V3 is applied through the milliammeter -55` (which enables the operator tov read the output) andl through junction'l 66 to the condenser C2 which accordingly `begins to charge. It will be recalled thatthe potential at point 56, immediately after discharge `o1' condenser C2, was approximately the potential' of line Lla, but as the charge isI accumulated on condenser C2, `the potential across that condenser increases proportional tothe quantum of charge and hence the potential at' junction 56 gradually drops by steps of varying amounts until `the potential at 56 approaches the potential that ls meanwhile being maintained constant atpoint 64.

When the potential at 56 thus decreases to approximately ithe same potential' as' is main'- tained at point B4, tube Vila becomes conductive, or stated another way, when condenser C2 has accumulated a predetermined amount quantity of electrical charge, tube Vdc becomes conductive. Then the following takes place in rapid sequence: Vda, becomes conductive and it therefore establishes `a circuit from .terminal K5 of condenser C2 to the cathode 5I of tube Vdc., thence to the anode 52 and through resistor R5, junction 33, line LIa, "to junction 35 which forms the other .terminal of condenser C2. Condenser C2 is thereby ldischarged through the resistor RF. The potential at ypoint d3 prior to tube Vdc becoming conductive, Iwas equal to the voltage of line Lid but when Vdc becomes conductive, the potential -at point 63 drops momentarily during the time that condenser C2 is discharging, due to 4the voltage drop across resistor R5. The drop in potential at .point 63 is transferred through condenser Cd to the grid 'II of tube V41). It will be remembered that tube VlIb has been conducting and its grid 'II during such period of con duc-tivity was maintained at the voltage of line L2 by virtue of the connection through resistor' R6. Momentarily, however, the voltage drop pulse at point t3, as transferred through condenser Cll causes the potential at point lil (namely grid lead ll) to be forced in a negative direcm tion in respect to line L2 and hence negative in respect to the cathode 66 from tube V41). This causes tube Vlib to become non-conductive and the potential at the anode terminal dit of tube V419 therefore approaches the potential of line Lia which therefore makes the grid "I2 of tube Vila even more positive with respect to the cathode than it had been as a result of the pulse transferred. As condenser C2 completes its `clischarge the potential ydrop across tube Vila becornes so Small that tube Vdc ceases to conduct. At this time the anode terminal t3, which during the discharge of condenser C2 had dropped in voltage below that of line Llc. (namely it had dropped to about 100 volts in the illustrated example) again swings sharply positivo towards the potential of line Lid. This applies a positive pulse through condenser Cd to the grid terminal 'I0 of grid 'Il of tube Vftb and the latter tube again becomes conductive. The conductivity of tube Vlb again being established causes the ipotential at its anode terminal t4 to swing from positive down towards negative voltage (namely towards about 100 volts in the illustrated eX- ample), and this potential swing is applied through line 'i3 to vthe grid 12 of tube Vdc which causes the latter to become even more sharply non-conductive.

The foregoing rapid sequence of events is carried out on a time scale determined by the time constants of the nip-flop circuit as is well known and occurs with great rapidity. The signal out put from tube Vllb occurs between terminals and 132.

Tube V5 is of the thyratron type, and during the time that it is non-conductive, its cathode 80 is held at a potential of about l0 volts in respect to line L12 by virtue of the potentiometer voltage divider circuit which begins at junction 3l on line LIa and continues through resistor Rl I to junction d2 which is the cathode terminal of tube V5, and thence through resistor Ril] to junction 83 on line L2. The resistors RIi and RII accordingly establish a potential at junction 82 which fixes the potential of the cathode 8@ of tube V5. During `such period of non-conductivity of tube V5, its control grid 84 is held negative (i. e. at the potential of line L2) by virtue of the connection through resistor R9 to junction 'I'I and thence through line 'I8 and resistor R8 to junction 'it on line L2. Accordingly, with the grid Si negative with respect to the cathode 80, tube V5 is non-conductive. Likewise, during such period of non-conductivity of tube V5 the voltage of its anode 38 is the same as 'the potential of line Ll due to the connection thereto through resistors RIZ, junction im and RI3 to junction 3i? on line Li. The circuit from junction dii on line L2, thence through resistor RIB to junction 9% and through condenser C'I to line L2 exerts full line voltage on condenser C'I and maintains that condenser charged. The condenser Ct is also charged during such period of non-conductivity of tube V5 by vir-tue of the connection of one of its terminals vthrough resistors Rl2 and Rit to line L! and by virtue of its connection through the coil d3 of the stepping relay and ythen through junction 492 and line 9|, junction iii/Z and resistor Ri@ to junction 83 on line L2.

When the signal pulse from the anode termin-al $4 of .tube Viib occurs, it is transferred through condenser C5 to junction l? and thence through resistor Re to the control grid gli of tube V5, and the grid then becoming positive with respect to the cathode causes tube V5 toconduct. When tube V5 thus becomes conductive, it serves as a circuit 'by iwhich the charge which, .as previously explained, had been stored upon condenser CB may readily be `permitted to dissipate through a circuit extending from one terminal of the condenser Ct, 'thence through the tube Vt which is then conductive, to junction S2 on the cathode lead of the tube and thence through line 9| to the coil 93 of the stepping relay and through line 9d to the other side of condenser CIS. Thus, the stored charge on condenser C6 is permitted to flow through the coil S3 of the stepping relay which causes the operation of the stepping relay through one pulse, causing the ratchet II i to be moved one step with consequent operation of the plunger of the hypodermic syringe through one increment of movement and hence one unit of anesthetic is administered to the patient. In the even-t an ether pump, such as vthat shown in Figure 10, is used, the pump operates one pulse and one unit by volume of ether is pumped to the respiratory mask or other ether inhalating device used on the patient. Such unit quantity of anesthetic from syringe MI -or from pump |50 is recorded on the traces shown in Figures l and 2, as the vertical mark or pip on such traces. The status of yconductivity of tube V5 causes little current to be drawn .through it from line LI :because or the combined resistances of resistors R23, REZ and Rl il in the circuit extending through tube V5 from line Li to line L2. Hence, tube V5 stops conducting when the charge on condenser C6 is dissipated lthrough the stepping relay or 'through the ether pump of Figure l0.

The sharp discharge of condenser C6 might cause a transient impulse to be imposed upon line LI under some conditions and in order to prevent any possible false signals being reflected back: to the input circuit of tube V3, there is provided condenser C'I as a reservoir of supply which serves to re-charge condenser Ct through resistor Ril?. As a further means of absorbing any `transient that might be impressed upon line LI and 'thence upon line Lic, there is provided 'the condenser C3 which stands connected gecoate l from. line Lla' to. line L2'. Any sharp= transient or' wave-front thus imposed/upon line L`|a` is absorbed by condenser C3 lwhich therefore; does not permit the transient to reach the input of tube V3.

Referring again to the correlated. recordings shown in Figures l and 2, it will be observed that thefpips. or short vertical markings recording the successive: injections of anesthetic occur onlyl withA moderate frequency when the patient islin' the restingv position. However, such input ofanesthetic causes the patient to progress to ther condition of light anesthesia, Where theincreased'brain wave signal results in a more frequent actuation of the anesthetic administering syringe or pump, as indicated by the more frequent short vertical markings or pips on the anesthetic record. rFliese more frequent'injec'- tions of anesthetic cause the patient to progress to-the. state of moderate anesthesia andas a result of the progress to suchv stage of moderate anesthesia, the brain wave of the patient decreases in activity as indicated by the recording so'marked. As a result of this decreased brain wave activity, the system causes a less frequent administration of anesthetic'. Depending upon the setting of resistor Rl, the patient may therefore be held in the condition of light`, moderate` or deep anesthesia. A point of equilibrium' is reached at any setting of resistor Rl, at which the ratey of infusion of the anesthetic drug balances the rate of removal or destruction of the anesthetic by the tissues'.

Thus, the system is put into operation by initially injecting a small amount of anesthetic agent intoithepatient. Uponl reaching the brain of the patient the anesthetic stimulates the cortical neurones and increases their electrical: output, and this in turn causes an increase in the rate of administration of the drug by action of the system. In this phase the system will be seen to be self-augmenting, or in= the parlance of. the electronic arts, it has the effect of a positive feedback. As soon as the drug reaches the concentration at which. suppressionl of cortical electrical activity of the patient commences, the system changes to a self-limiting system, or in electronic parlance, it reaches a state of negative feed-back. It is in this phase that the system settles into equilibrium and maintains a depth of anesthetic which is dependent upon the adjustment of resistor R|.

Because of the feed-back characteristic of the system during operation, the apparatus has some of the properties of a hemostatic system, and the system accordingly tends to compensate for factors which disturb' the equilibrium. For example, if a leak should develop in the tube lead-- ing to thev patient for making intravenous injections of the anesthetic, or should a leak develop or dilution occurl in the administration of ether. by lway oi respiratory system or otherwise, the machine automatically increases its rate of administration in an attempt to compensate for the attendant losses of anesthetic. Complete compensation is not, however, attained since the system as a whole has a dropping stimulus-response curve similar to the speed-load curve of a governor-steam engine system. A change in received stimulus which in this illustration is the brain wave signal results in a relatively slight shift of the system to a new equilibrium point on the stimulus-response curve, in aA manner analogous to the shift in equilibrium-*of a governor-steam'engine system where load changes.

I6 By4 utilizingl thefsystem, animals have been kept automatically anesthetized for periods up tof two orthree days without circuit readjustment, and the system has beeng used with completev condence onl human beingsffor anesthetization during. operative procedures.

Referring to Figure 11., the connections tothe patient by means of the scalp hooks I0, |2 and |'|J are identicaly with those previously described withirei'erence'to Figure 3. 'I'he brain-wave signal as picked' up byI such connections I0, and lf2", however, is in this instance applied to the input terminals-164; |68 and `ground terminal. |466 of a battery operated preamplifier generally designated |61. The battery operated preamplifier |r61 isoff the: push-pull type andwhasoutput terminals |68 and.- |B9 which are connected to the input terminals |1l| and. |15 of avariable bandpassf filter generally designated |10. The bandpass filter' is designed so asto permit frequencies in the range of approximately three cycles per second to 30 cycles-per second tol be passed. there through tothe. output terminals' |16 and |-11 which are connected to the inputterminals |110 and |19 of a. push-pull power amplier` generally designated |00A having. output terminals and |02. The terminal |82 isfconnected tothe grid lead49 and terminal` |18| is connected tolineLZ. The-anesthesia administering circuits shown under the bracket. II. of Vlligure 11' arev identical with those previously described withreferencev tov Figure 3 andhence need no further description.

In operation the system shown in Figure 11- is responsive tothose frequencies of the brain wave signal in the range of about 3 to about 30- cycles only and hence the systeml is not disturbed by slow voltage shifts which not infrequently may be found to occur in operatingV rooms due to the accumulation of a staticcharge on portions of the system, as for example may occur when one of the attendants or surgeons may havevshoes which are rubber soled, thereby applying to the patient a static voltagewhich may then be reilected as. a slow shift in voltage on thev brain wave signal circuits connected to the patient. Likewise, high frequency apparatus, such as diathermy apparatus or X-ray equipment causes no ill eifects when utilizing the band-pass lter |10 in the circuit.

Referring to Figure 12 the apparatus includes between the patient and the anesthesia administering. circuits shown under the bracket II a comparator shown generally over the bracket V. This comparator circuit receives the brain wave signal by virtue of the connections IU, and l2, as previously described, which are impressed upon the leads |90, groundv lead |9| and lead". |92, respectively. Leadv is connected to the control grid |9`3` of an amplier tube generally designated |94 which is housed in the chassisi'QS that is connected to the ground line |91. The tube |94isvprovided` with yan anode |198 that is connected through. line |91 to terminal |38 `on" tiielineLla which has a regulated voltage as previously described. ,The indirectly heated cathode 200 of the tube |94 i's connected through junction '20| and resistor v202 to junction 203 on line`L2, The resistor 202 is bridgedby a condenser 205, that i's connected to junction `20| via line 206 `and junction 201, and is'connected to line L2 at; `junction 208. Accordingly; the signal1 input tothe amplifier |94"v is impressed upon control grid rsl'and line- L2` and tube |94 becomes conductive and currentflows through its cathode-anode circuit which-isn proportional al- Ways to the input signal, thereby causing the voltage at point 20| to vary in accordance With such input signal. From terminal 20| on the cathode, lead line 206 extends through junction 201 and junction 2|() to one terminal of resistor 2| the other terminal of said resistor being connected through line 2 I2 to the negative terminal 2|3 of a bias battery 2|5, the positive terminal of which is connected back to junction 2|. The battery 2 I5 accordingly imposes a continuous potential across resistor 2| I andv by virtue of the variable tap 2| 6 a selected portion of this voltage is subtracted from the potential at point 20| and it is accordingly this difference in potential which is then applied to line 2|8 that controls the control grid 4| of the tube V3. As a result the amplified input signal of the brain Wave pattern is compared to a datum potential, namely a selected portion of the potential of battery 2|5 and any difference in potential between the signal and such datum or deviation in potential is then applied to line 2|8 is the signal potential for actuating tube V3. The system accordingly operates on the error-actuated principle rather than on the drooping-characteristic principle as explained with reference to the system shown in Figure 3. The system shown in Figure 12 has especial advantage because of its high sensitivity to change.

The herein described system and method can be used without modification for automatic anticonvulsive therapy for conditions such as continuous epileptic seizure, i. e. status epilepticus. 1n this condition continuous high voltage brain waves (up to one millivolt) having predominate frequencies in the range of 3 to 10 cycles per second are present as long as such seizures continue. For treatment, the brain Wave signal (electroencephalographic potential) is picked up as previously described. If the system of Figure 11 is being used, band pass filter |10 is adjusted (or designed) to pass the 3 to 10 cycles frequency band. Syringe |4| is then filled with an anticonvulsant drug such as pentothal, luminal or amytal and administered intravenously. The effect of such drugs is to decrease the seizure and also the brain wave signal, with the result that the patient is gradually brought down to a condition where the brain Wave pattern is normal, that is to say there is a reduction of several hundred per cent fall in integrated potential output of the brain Wave.

Where the system is used for continuous control of heart function a suitable drug is chosen for the treatment and in this case the incoming signal is an electrocardiogram or the pulse rate may be translated as a generated electrical signal (by microphone for example) and utilized as the incoming signal of the apparatus. In similar manner respiratory signals, skin temperature signals, etc. may be picked up and utilized for the automatic administration of the appropriate drugs.

As many apparently widely different embodiments of this invention may be made Without departing from the spirit and scope thereof, it is to be understood that I do not limit myself to the speciiic embodiments herein.

What I claim is:

1. An automatic apparatus for administering material to a patient comprising an amplifier having an input connectable to a patient and an output for amplifying a physiological electrical potential of a patient, capacitor means connected to the output of said amplifier for storing and integrating said amplified signal, means connected to said capacitor means and connectable to said patient, said means being responsive to the quantum of stored integrated electrical charge of said capacitor means when the quantum of charge reaches a predetermined value for administering to the patient a predetermined amount of said material and for simultaneously dissipating said charge.

2. An automatic apparatus for administering to a patient material which varies the physiological electrical output of the patient comprising an amplifier having input and output terminals, said input terminals being adapted to be connected to the patient for obtaining a physiological electrical output signal from the patient, means connected to the output of the amplifier for integrating said physiological output signal, said means including means connectable to the patient for moving said material to said patient at a rate proportional to the integrated physiological electrical output signal of the patient.

3. An automatic apparatus for administering to a patient material which varies the electroencephalographic potential of said patient comprising an amplifier having input and output terminals, said input terminals being adapted to be connected to the head of a patient for obtaining an electroencephalographic potential signal from said patient, integrating means for integrating said electroencephalographic potential signal and means connected to said integrating means including means connectable to said patient for moving said material to said patient at a rate proportional to the integrated electroencephalographic potential signal of said patient.

4. An automatic apparatus for administering to a patient material which varies the physiological electrical output of the patient comprising an amplier having input and output terminals, means for connecting the input terminal to a patient for obtaining said physiological electrical output signal from said patient, motor means connected to the output terminals of said amplifier and material feeding means connected to and driven by said motor means and having a material delivery outlet adapted to be connected to the patient for delivering material to the patient in response to the amplified physiological electrical output signal received from the patient.

5. An automatic apparatus for administering to a patient material which varies the physiological electrical potential of said patient comprising an amplifier having input and output terminals, said input terminals being adapted to be connected to a patient, energy storing means connected to the output terminals of said amplifier for accumulating electrical energy in proportion to the integral of the amplified potential output of the patient, material transferring means having a material delivery outlet adapted to be connected to said patient, said transferring means being also connected to said energy storing means and movable in response thereto, for delivering a prescribed amount of material to said patient when the charge in said energy storing means reaches a predetermined amount and simultaneously dissipating said charge preparatory to accumulating another charge.

6. An automatic apparatus for administering anesthetics and the like materials to patients comprising means having input terminals adapted to be connected to the patient Who is to be anesthetized for impressing the electroencephalographic potential of said patient on said input terminals, said means including a device for accumulating an electrical charge at a rate proportional to the integral of the amplified electroencephalographic potential signal of the patient being anesthetized, and means connected to said device for accumulating said charge and responsive to each predetermined accumulation of charge thereon for administering a predetermined amount of said anesthetic or the like material to the patient.

i 7. An automatic apparatus for administering anesthetics or the like materials to a patient comprising means having input terminals adapted to be connected to a patient who is to be anesthetized and including `means for accumulating an electrical charge at a rate proportional to the integral of the electroencephalographic potential signal of said patient being anesthetized, and means connected to said means for accumulating said charge and responsive to a predetermined accumulation of charge thereon for administering to the patient a predetermined amount of anesthetic or the like material and for simultaneously dissipating said charge on said means for accumulating said charge.

8. An automatic apparatus for administering anesthetics and the like materials to patients comprising means having input terminals adapted to be connected to a ypatient who is to be anesthetized, said means including an amplifier having output terminals, condenser means connected to said amplifier output terminals for storing and integrating the resultant amplified output, a discharge circuit connected to said condenser means and through which said condenser may discharge when the potential of said condenser means reaches a predetermined value, and motor transfer means connected to said discharge circuit and responsive to the discharge of said condenser means for moving predetermined amounts of said material to the patient.

9. An automatic apparatus for administering anesthetics and the like materials to patients comprising means having input terminals adapted to be connected to a patient who is to be anesthetized, said means including an amplifier having output terminals, condenser means connected to said amplifier output terminals for storing and integrating the resultant amplified output, a discharge circuit connected to said condenser means and through which said condenser may discharge when the potential of said condenser means reaches a predetermined value, a triggering circuit connected to and responsive to the potential of the condenser means for discharging the condenser through said discharge circuit, and motor transfer means connected to said discharge circuit and responsive to the discharge of said condenser means for moving predetermined amounts of said material to the patient.

l0. The apparatus of claim 9 further characterized in that said triggering circuit comprises a. flip-flop circuit.

11. An automatic apparatus for administering anesthesia to a patient comprising an amplier having, input and output terminals, said input terminals being adapted to be connected to the scalp of the patient for supplying to the input terminals the electroencelphalographic potential of said patient, an anesthetic supply reservoir, transfer means connected to said supply reservoir for moving the anesthetic from the supply reservoir, said transfer means being adapted to be connected to the patient, and means connected to the output of said amplier and to said transfer means for integrating they amplified` electro- 20 encephalog'raphic potential signal of said patient and for actuating said transfer means so as to transfer to the patient a predetermined amount of anesthetic when the integral of the electroencephalographic potential signal of the patient reaches a predetermined amount.

12. An automatic device for administering anesthetics and the like to patients comprising an amplifier having input and output terminals, said input terminals being adapted to be connected to the patient for receiving from the patient a. physiological electrical output signal, said amplifier including means for rectifying the signal so received, a condenser connected to the output of said amplifier for storing said rectified signals, an auxiliary circuit connected to said condenser for discharging it when the condenser becomes charged to a predetermined voltage, thereby permitting said condenser to begin recharging immediately, a material supply and material pump means connected to said auxiliary circuit so as to be actuated thereby for pumping measured amounts of said material to the patient each time said condenser is discharged through said auxiliary circuit.

13. An automatic apparatus for administering anesthetics and the like materials to a patient comprising an amplifier having input and output terminals, said input terminals being adapted to be connected to the head of a patient for obtaining an electroencephalographic potential signal from the patient, a band pass filter capable of transmitting electrical signals in the frequency range of 3 to 30 cycles per second connected to the output and said amplifier, and acumulator means connected to said band pass ilter and responsive to the signals transmitted therethrough for integrating and accumulating said signals, and material supply and transfer means adapted to be connected to the patient and connected to said accumulator means and responsive to the integral of the transmitted signal thereon when said integral reaches a predetermined amount for transferring to the patient a predetermined quantity of. said material.

14. An automatic apparatus for administering anesthetics to a patient comprising means for amplifying a received el'ectroencegihalographic` potential signal of the patient, said means having input terminals adapted to be connected to the patient and having. output terminals. a band pass filter transmission network connected to output terminals of said amplifier, said filter network being connected to accumulator means for integrating said signal and material delivery means connected to said accumulator means and adapted to be connected` to the patient for delivering material to said patient at a rate proportional to said integratedI signal.

15. An apparatus for administering anesthetics and the like materials to a patient comprising an ampliiier having input terminals adapted to be connected to the patient for receiving an electroencephalographic potential signal from` the patient, said ampliier having output terminals, a. potential source yforming a comparison voltage connected to said output terminals and means for accumulatingv a charge proportional to the difference between the amplied signal received. from the patient and said. comparison` voltage; and material transferring means connected. to' said means for accumulating said charge anni` adapted to be connected to the patient for transferring material to the patient at a rate pro- 2l portional to the rate of accumulation of said charge.

16. An apparatus for administering anesthetics and the like materials to a-patient comprising an amplier having input and output terminals, said input terminal being adapted to be connected to the head of a patient for receiving the electroencephalographic potential signal from the patient, said output terminal being connected to a potential source forming a voltage vof comparison, means for accumulating a charge connected to said potential source and said output terminals of the amplier for accumulating a charge proportional to the difference between an amplified electroencephalographic potential signal and said voltage of comparison, material transfer means connected to said means for accumulating said charge and adapted to be connected to said patient for transferring a predetermined amount of said material to the patient each time the 22 charge accumulated on said means for accumulating reaches a predetermined amount, and means connected to said means for accumulating Ia charge for dissipating the charge thereon as said predetermined amount of material is transferred to the patient.

References Cited in the le of this patent UNITED STATES PATENTS Number Name Date 978,728 Frink Dec. 13, 1910 2,225,201 Anderson Dec. 17, 1940 2,254,833 Ashkenaj Sept. 2, 1941 2,409,033 Garceau Oct. 8, 1946 2,416,158 Coykendall Feb. 18, 1947 2,419,682 Guillemin Apr. 29, 1947 2,457,744 Sturm Dec. 28, 1948 2,457,977 Cookson Jan. 4, 1949 2,498,672 Glass Feb. 28, 1950 

